Ophthalmologic image processing method and storage medium storing program for executing the method

ABSTRACT

An ophthalmic image processing method includes: acquiring information about characteristics of an examinee&#39;s eye including corneal information about the corneal anterior surface shape of the examinee&#39;s eye, and refractivity information about refraction of the examinees eye as a whole; generating a simulation image of a target image formed at fundus of the examinee&#39;s eye using the refractivity information; and simultaneously displaying an eyeball model image showing an eyeball structure, the simulation image, and a corneal information image associated with the cornea on the eyeball model image and corresponding to the corneal information.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims priority from Japanese Patent Application No.2014-018716 filed with the Japan Patent Office on Feb. 3, 2014, theentire content of which is hereby incorporated by reference.

BACKGROUND

1. Technical Field

The present disclosure relates to an ophthalmic image processing methodfor displaying characteristics of an examinee's eye obtained by anoptometry apparatus, and a storage medium having a program for executingthe method stored therein.

2. Description of the Related Art

Conventionally, a device is known that integrally displays imagesshowing information about characteristics of various locations of anexaminee's eye that are obtained by an optometry apparatus. For example,in a device described in JP-A-2010-201072, a wavefront aberrationanalysis map and a corneal anterior surface shape analysis map aresimultaneously displayed.

There is also known a device that simulates, using software, how atarget image appears to the examinee's eye of which a refractive erroris corrected with an eyeglass lens and the like, based on the wavefrontaberration data of the examinee's eye. For example, JP-A-2013-236902discloses simulation about the way a target image appears to theexaminee's eye wearing an intraocular lens.

SUMMARY

An ophthalmic image processing method includes: acquiring informationabout characteristics of an examinee's eye including corneal informationabout the corneal anterior surface shape of the examinee's eye, andrefractivity information about refraction of the examinee's eye as awhole; generating a simulation image of a target image formed at fundusof the examinee's eye using the refractivity information; andsimultaneously displaying an eyeball model image showing an eyeballstructure, the simulation image, and a corneal information imageassociated with the cornea on the eyeball model image and correspondingto the corneal information.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram of the overall configuration of an ophthalmicinformation processing device according to an embodiment.

FIG. 2 is a flowchart of the flow of processing by an ophthalmicinformation processing program.

FIG. 3 illustrates examples of images displayed on a monitor as a resultof execution of the ophthalmic information processing program.

FIG. 4 is a flowchart of the flow of processing by the ophthalmicinformation processing program in a modification.

DESCRIPTION OF THE EMBODIMENTS

In the following detailed description, for purpose of explanation,numerous specific details are set forth in order to provide a thoroughunderstanding of the disclosed embodiments. It will be apparent,however, that one or more embodiments may be practiced without thesespecific details. In other instances, well-known structures and devicesare schematically shown in order to simplify the drawing.

However, in the device described in JP-A-2010-201072, images showinginformation about the characteristics of various locations are simplyarranged on the screen. In the device described in JP-A-2013-236902,simulation images and the like are simply arranged on the screen. Thus,in these devices, it may be difficult for a person not familiar withexaminations to understand the information and/or images.

An object of an embodiment of the present disclosure is to provide anophthalmic image processing method for enabling information and/or animage to be displayed in a readily and intuitively understandablemanner, and a storage medium having a program for executing the methodstored therein.

An ophthalmic image processing method according to an embodiment of thepresent disclosure includes: acquiring information about characteristicsof an examinee's eye including corneal information about the cornealanterior surface shape of the examinee's eye, and refractivityinformation about refraction of the examinee's eye as a whole;generating a simulation image of a target image formed at fundus of theexaminee's eye using the refractivity information; and simultaneouslydisplaying an eyeball model image showing an eyeball structure, thesimulation image, and a corneal information image associated with thecornea on the eyeball model image and corresponding to the cornealinformation.

A non-transitory storage medium according to an embodiment of thepresent disclosure having a computer program for causing a computer tofunction as an ophthalmic information processing device stored therein,the ophthalmic information processing device performs: acquiringinformation about the characteristics of an examinee's eye includingcorneal information about a corneal anterior surface shape of theexaminee's eye and refractivity information about refraction of theexaminee's eye as a whole; generating a simulation image of a targetimage formed at the fundus of the examinee's eye using the refractivityinformation; and simultaneously displaying an eyeball model imageshowing an eyeball structure, the simulation image, and a cornealinformation image associated with the cornea on the eyeball model imageand corresponding to the corneal information.

According to an embodiment of the present disclosure, information and/oran image can be displayed in an easily and intuitively understandablemanner.

In the following, an embodiment of the present disclosure will bedescribed with reference to the drawings. First, with reference to FIG.1, the overall configuration of an ophthalmic information processingdevice 1 that executes an ophthalmic information processing programaccording to the present embodiment will be described. According to anembodiment of the present disclosure, an ophthalmic image processingmethod which will be described later may be implemented by having theophthalmic information processing program executed by a processor of theophthalmic information processing device 1.

The ophthalmic information processing device 1 (hereafter simplyreferred to as “the processing device 1”) according to the presentembodiment simulates the way a target image appears to the examinee'seye by processing information about refraction of the examinee's eye. Asa result, a simulation image concerning the way the target image appearsis generated. While the details will be described later, the simulationimage may include an image showing the way the target image appears tothe examinee's eye of which refractive error is corrected, as well as animage showing the way the target image appears to the naked eye. Theprocessing device 1 according to the present embodiment outputs, besidesthe simulation image, characteristics information images (such as acorneal anterior surface shape analysis map, an aberration map, and aretro-illumination image) showing information that the examinee's eyehas concerning the characteristics of an eye optical system. While thedetails will be described later, the processing device 1 according tothe present embodiment further displays am eyeball model image showingthe structure of the eyeball so that the relevance between thesimulation image and the characteristics information images can beintuitively known.

In the present embodiment, the processing device 1 is provided with aCPU (operating and processing unit) 30, a storage unit (memory) 35, anoperation input unit (hereafter referred to as an input unit) 40, amonitor 50, and an image processing unit 31. These units are mutuallyconnected via a bus and the like. To the processing device 1 (CPU 30), aprinter 43 is connected.

The CPU 30 is a processor (a computer or a part thereof) that controlsthe operation of the various units in accordance with a program. Theinput unit 40 is an input device operated by an examiner. Examples ofthe input unit 40 include a switch, a keyboard, and a pointing device(such as a mouse and touch panel). The image processing unit 31 performsvarious image processes on the basis of a command from the CPU 30. Theimage processing unit 31 also displays various images and the like on adisplay screen of the monitor 50 on the basis of a command from the CPU30. The storage unit 35 stores various programs executed by the CPU 30,for example. An ophthalmic information processing program which will bedescribed later is also stored in the storage unit 35. Examples of thestorage unit 35 include a semiconductor memory, a magnetic storagedevice, and an optical storage device. The monitor 50 is used as anoutput device (display device) and controlled by the CPU 30. The monitor50 according to the present example is a touch panel enabling an inputoperation by the examiner, and includes the function as the input unit40.

The ophthalmic information processing program and various programs maybe recorded in a non-transitory, computer-readable recording medium(“recording medium”), such as an optical disk, a magnetooptic disk, amagnetic disk, or a flash memory. The programs may also be provided viaan information communication line, such as the Internet.

To the processing device 1, there may be connected an optometryapparatus for obtaining information about the characteristics of theexaminee's eye (hereafter referred to as “characteristics information”).For example, in the present embodiment, mainly an anterior segmentmeasuring apparatus 10 is connected to the processing device 1. Theprocessing device 1 and the anterior segment measuring apparatus 10 mayhave separate housings. In this case, a general-purpose computer capableof executing the ophthalmic information processing program (such as aPC) may be used as the processing device 1. The processing device 1 andthe anterior segment measuring apparatus 10 may be integrated. In thiscase, the CPU 30 of the processing device 1 may be configured to controlthe various units of the anterior segment measuring apparatus 10.

The anterior segment measuring apparatus 10 is used for measuringoptical parameters in the anterior segment (including the cornea, theiris, the crystalline lens, and the like). For example, the anteriorsegment measuring apparatus 10 according to the present embodimentirradiates the cornea of the examinee's eye with measurement light andreceives reflected light to measure the shape of the cornea (including,at least, the shape of the corneal anterior surface) of the examinee'seye. The corneal anterior surface shape data obtained by the anteriorsegment measuring apparatus 10 is analyzed to provide variousinformation about the shape of the corneal anterior surface, such asrefraction data (for example, refractivity distribution), curvature data(for example, curvature distribution), and three-dimensional shape dataand aberration data (such as aberration map data and high-orderaberration map data).

Hereafter, the anterior segment measuring apparatus 10 according to thepresent embodiment will be described as a device for measuring opticalparameters in the anterior segment (such as the shape of the cornealanterior surface) by projecting a placido target onto the cornea of theexaminee's eye and receiving the reflected light. In another embodiment,the anterior segment measuring apparatus 10 may include a device thatmeasures the optical parameters in the anterior segment using an opticalinterference principle (anterior segment optical coherence tomography).

The anterior segment measuring apparatus 10 in the present exampleincludes a placido plate 11, an illumination light source 12, ananterior segment imaging optical system 15, and a control unit 16. Inthe placido plate 11, a number of placido rings are formed. Theillumination light source 12 illuminates the ring patterns of theplacido plate 11 substantially uniformly with respect to the examinee'seye. The anterior segment imaging optical system 15 includes aphotography lens 13 and a two-dimensional imaging element 14. Theanterior segment imaging optical system 15 captures a ring pattern imageprojected on the cornea of the examinee's eye using the two-dimensionalimaging element 14. The ring pattern image is analyzed to obtaininformation about the shape of the corneal anterior surface.

In the present embodiment, the anterior segment imaging optical system15 captures an anterior segment image including the pupil portion of theexaminee's eye. From the anterior segment image, the pupil diameter ofthe examinee's eye is measured, for example. The anterior segmentmeasuring apparatus 10 may be configured to image the examinee's eyewhile switching the amount of illuminating light. For example, theanterior segment imaging optical system 15 may capture the anteriorsegment image of the examinee's eye in each of photopic vision andtwilight vision. In this case, the illumination light source 12 may beconfigured such that its output (the amount of light) is adjustable to afirst illumination light amount for photopic vision photography and asecond illumination light amount for twilight vision photography whichis smaller than the first illumination light amount.

The anterior segment measuring apparatus 10 according to the presentembodiment is further provided with a measuring optical system (such asthe phase difference system disclosed in JP-A-10-108837, or an eyeaberration meter using a Shack-Hartmann sensor), which is not shown. Themeasuring optical system measures refraction data, wavefront data andthe like of the examinee's eye as a whole by projecting a measurementlight flux onto the examinee's eye and receiving fundus reflected lightfrom the measurement light flux.

The anterior segment measuring apparatus 10 may be configured to capturean inner-pupil image (a so-called retro-illumination image) of theexaminee's eye. For example, the anterior segment measuring apparatus 10projects illuminating light into the pupil of the examinee's eye byswitching on a measuring light source of a measuring optical system thatmeasures the refraction data and wavefront data and the like of theexaminee's eye as a whole. The anterior segment measuring apparatus 10further produces an image projected on an imaging element, which is notshown, using fundus reflected light obtained as the illuminating lightis reflected by the fundus. Thus, a retro-illumination image iscaptured.

The processing device 1 and the anterior segment measuring apparatus 100are connected by a LAN and the like. Thus, the information obtained bythe anterior segment measuring apparatus 10 is transferred to thestorage unit 35 of the processing device 1.

The processing device 1 is connectable with an ophthalmic apparatus 60(such as an ocular axial length measuring apparatus or optical coherencetomography) other than the anterior segment measuring apparatus 10.Thus, the processing device 1 can obtain characteristics informationwhich is difficult to obtain with the anterior segment measuringapparatus 10 (such as ocular axial length data and cross section imagedata of the cornea or the fundus).

With reference to the flowchart of FIG. 2, an example of the processperformed by the processing device 1 by having the ophthalmicinformation processing program executed by the CPU 30 will be described.

First, in an eye information acquisition process (S1: acquisition step),characteristics information of the examinee's eye is acquired by theprocessing device 1. The characteristics information obtained by theprocess of S1 includes corneal information about the anterior surfaceshape of the cornea of the examinee's eye and refractivity information.The corneal information includes, for example, the corneal anteriorsurface's three-dimensional shape data, curvature data, refraction data,and aberration data. The refractivity information is information aboutrefraction of the examinee's eye as a whole, and includes, for example,refraction data and aberration data.

In the present embodiment, there is further obtained intraocularinformation as characteristics information. The intraocular informationincludes at least one of information about the opacity in the examinee'seye, and information about refraction in the examinee's eye except forthe corneal ante or surface. The intraocular information includes, forexample, information indicating the degree of opacity in the examinee'seye, and refraction data and aberration data in the examinee's eyeexcept for the corneal anterior surface. Size information about theexaminee's eye (such as pupil diameter data and ocular axial lengthdata) may be acquired as characteristics information. Thecharacteristics information may be in the form of a result ofmeasurement of the examinee's eye by the optometry apparatus (such asthe anterior segment measuring apparatus 10), or image data of an imagecaptured by the optometry apparatus (such as an anterior segment image,a ring pattern age, or a retro-illumination image).

While details will be described later, in the present embodiment, thecharacteristics information acquired by the process of S1 (morespecifically, the refractivity information of the examinee's eye as awhole) is utilized to generate a simulation image showing the way atarget image appears to the examinee's eye (see S3). The characteristicsinformation obtained by the process of S1 is also utilized to displaythe characteristics information image of the examinee's eye (see S4).

In the present embodiment, the process of S1 will be described as aprocess of transferring the measurement result and images and the likeobtained by the optometry apparatus connected to the processing device 1to the storage unit 35 and the like. However, the process content is notnecessarily limited to the above. For example, the process of S1 mayinclude a process of feeding the measurement result and the like of theexaminee's eye obtained by the optometry apparatus and stored in anexternal storage device to the storage unit 35. The process of S1 mayalso include a process of obtaining, as characteristics information, aresult of analysis (analysis result) of the measurement result and thelike obtained by the optometry apparatus. Obviously, the process of S1may include a process combining the above processes.

In a correction data acquisition process (S2: correction dataacquisition step), correction data of a corrective lens for correctingthe refractive error of the examinee's eye is acquired by the processingdevice 1. In the present embodiment, a case will be described in whichthe corrective lens is an eyeglass lens. The corrective lens, however,may be a contact lens or an intraocular lens and the like. Thecorrection data may include, for example, actual lens meter data; ameasurement result by an auto refractometer, a wavefront sensor and thelike; a subjective examination result; or an examiner input value. Thecorrection data may further include information about the distance fromthe examinee to the target (use distance information), or information(lens placement interval information) about the interval between theexaminees eye and the corrective lens (corrective lens placementinterval). Hereafter, the process of S2 will be described as a processof the CPU 30 acquiring, as correction data, lens parameters (such asthe values of S (spherical diopter power), C (cylindrical diopterpower), and A (astigmatic axial angle)) that are input by an inputoperation by the examiner using the input unit 40. The process of S2 isnot necessarily limited to the above. For example, the process of S2 mayinclude a process of the processing device 1 receiving correction datafrom the ophthalmic apparatus, an external storage device and the likeconnected to the processing device 1.

The correction data acquired by the process of S2 are utilized, togetherwith the refractivity information of the examinee's eye, for generatinga simulation image. The processing device 1 according to the presentembodiment may be configured to generate the simulation in age of thetarget image formed at the fundus of the examinees eye wearing acorrective lens (a wearing simulation image). The processing device 1may also be configured to generate the simulation image of the targetimage formed at the fundus of the naked eye (non-wearing simulationimage). For example, the non-wearing simulation mage may be generatedwhen the spherical diopter power S and the cylindrical diopter power Cof the correction data are 0 (D), or when an instruction for performingsimulation in the naked eye state is received via the input unit 40.

Then, in the flowchart of FIG. 2, a simulation image generating process(S3: generating step) is executed by the CPU 30. In the process of S3,the CPU 30 generates the simulation image on the basis of at least therefractivity information of the examinee's eye as a whole acquired bythe process of S1 (S3). The simulation image represents the target imageformed at the fundus (retina) of the examinee's eye. Namely, the way thetarget image appears to the examinee's eye is shown by the simulationimage.

In the process of S3, the simulation image may be generated usingvarious targets. For example, in the present embodiment, there aregenerated a first simulation image 105 showing the way one or aplurality of subjective examination targets (such as a visual acuityexamination target, an astigmatism target, and a screening target)appear, and a second simulation image 106 showing the way a point image(point target) appears (see FIG. 3). The first simulation image 105 isobtained by a simulation sing a subjective examination target (firsttarget). The second simulation image 106 is obtained by a simulationusing a point image (second target).

The second simulation image 106 may be an image two-dimensionallyshowing a point image strength distribution (PSF) obtained by subjectingthe wavefront aberration of the examinee's eye to Fourier transform. Thefirst simulation image 105 is obtained, for example, by multiplying anoptical transfer function (OTF) obtained by further Fourier transform ofthe point image strength distribution (PSF) with the space frequencydistribution of the subjective examination target.

In the present embodiment, the corrective lens correction data acquiredby the process of S2 is incorporated into simulation. In this case, asthe simulation images 105 and 106, the above-described wearingsimulation image is generated using at least the correction data and therefractivity information of the examinee's eye. The wearing simulationimage is a simulation image of the target image formed at the fundus ofthe examinee's eye wearing a corrective lens. In the process of S3, thenon-wearing simulation image may be generated as the simulation images105 and 106. The non-wearing simulation image is a simulation image ofthe target image formed at the fundus of the examinee's eye not wearinga corrective lens (i.e., of the naked eye). The non-wearing simulationimage is generated using at least the refractivity information of theexaminee's eye.

Further, in the present embodiment, as the effective pupil diameter usedfor simulation, the pupil diameter of the examinee's eye in photopicvision and the pupil diameter of the examinee's eye in twilight visionare used. Which of the two types of pupil diameters are used may bedetermined in accordance with the examinee's eye environment duringsimulation. More specifically, when the simulation image in photopicvision is generated, data of the pupil diameter of the examinee's eye inphotopic vision are used. When the simulation image in twilight visionis generated, data of the pupil diameter of the examinee's eye intwilight vision are used. The photopic vision pupil diameter data andthe twilight vision pupil diameter data are, for example, measured froman anterior segment image in photopic vision and an anterior segmentimage in scotopic vision, respectively. The examinee's eye environmentthat is set at the time of simulation may be set by the examiner via theinput unit 40 (as will be described in detail below).

In the device according to the present embodiment, the distance betweenthe examinee's eye and the subjective examination target, and theinterval at which the corrective lens is disposed with respect to theexaminee's eye that are used during simulation may be constant values oradjustable values. When these values are adjustable, values based on thecorrection data acquired in the process of S2 may be used, or separatelyacquired values (such as values input by an operation on the input unit40) may be used.

Next, according to the flowchart of FIG. 2, a display control process(S4: display control step) is executed by the CPU 30. As a result, aneyeball model image 101, simulation images 105 and 106, and an imageindicating the state of the eye optical system are displayed on themonitor 50 (see FIG. 3).

The eyeball model image 101 shows the structure of the eye. In thepresent embodiment, as the eyeball model image 101, a schematic viewshowing the three-dimensional eye structure of the eyeball as seenthrough diagonally is used. Alternatively, as the eyeball model image101, a cross-sectional view (or a cross-sectional schematic view) of asection perpendicular to a front-rear direction axis (such as the visualaxis) may be used, for example. In FIG. 3, the eyeball model image 101shows the overall shape of the eye. However, the eyeball model image 101is not limited to the above, and may be set to show a partial structureof the eye. For example, the eyeball model image 101 may be an imageonly of an anterior segment portion including the cornea and thecrystalline lens. In the present embodiment, the eyeball model image 101has a shape (structure) that has no relationship to the actual shape ofthe examinee's eye. However, this is not a limitation, and the eyeballmodel image 101 may be formed on the basis of shape data of theexaminee's eye measured by an optometry apparatus using OCT and thelike.

The eyeball model image 101 shown in FIG. 3 includes a cornea graphic102 representing the cornea at the position of the cornea. At thepositions of the crystalline lens and the fundus of the eyeball modelimage 101, a crystalline lens graphic 103 representing the crystallinelens and a fundus graphic 104 representing the fundus are formed,respectively.

On the eyeball model image 101, information indicating the shape of theexaminee's eye may be displayed. For example, in addition to the corneacurvature shown in FIG. 3, there may be shown on the eyeball model image101 measurement values of the ocular axial length, corneal thickness,anterior chamber depth, crystalline lens thickness, vitreous bodythickness, pupil diameter, and corneal diameter and the like (namely,examinee's eye size information).

The monitor 50 also displays the simulation images 105 and 106 generatedby the process of S3. In the present embodiment, the first simulationimage 105 showing the way the subjective examination target appears isdisposed forwardly in the direction of the visual line of the eyeballmodel image 101 (or, when a lens graphic 110 which will be describedbelow is disposed, even forwardly of the graphic). In the presentembodiment, the second simulation image 106 showing the way the pointimage appears is displayed in association with the fundus of the eyeballmodel image 101. As shown in FIG. 3, a visual acuity chart is used asthe first simulation image 105. In the visual acuity chart, a pluralityof visual acuity examination targets is arranged according to eyesightvalues. As shown in FIG. 3, the monitor 50 may display information(numerical values and the like) indicating the distance between thesubjective examination target and the examinee's eye (or, the eyeglasslens) in simulation.

As shown in FIG. 3, in the present embodiment, the first simulationimage 105 and the second simulation image 106 are simultaneouslydisplayed in the same screen by the process of S4. Thus, the examinercan simultaneously confirm an overall result of visual perception by theexaminee's eye in accordance with the first simulation image, and thedetails of image blurriness in accordance with the second simulationimage 106 (more specifically, the direction, degree, and the like ofimage blurriness). Accordingly, the examiner can set corrective lensprescription values easily and well. In the present embodiment, thephrase “a plurality of images is simultaneously displayed” means that aplurality of images becomes visually perceptible at once.

Also by the process of S3, both a wearing simulation image about theexaminee's eye wearing a corrective lens and a non-wearing simulationimage about the examinee's eye not wearing a corrective lens may begenerated. In this case, in the present embodiment, a process ofselectively displaying one of the in ages on the monitor 50 is performedin the process of S4. For example, the CPU 30 may be configured toselect in a mode selection process which image is displayed in theprocess of S4.

FIG. 4 shows a flowchart of the ophthalmic information processingprogram in the case where the mode selection process is performed. Inthe flowchart, the mode selection process (S0: mode selecting step) isshown as an initially performed process. However, this is not alimitation, and the mode selection process is only required to beperformed prior to the display control process (S4).

In the mode selection process, the CPU 30 selects one display mode froma plurality of display modes. The plurality of display modes includes afirst display mode in which the wearing simulation image is displayed,and a second display mode in which the non-wearing simulation image isdisplayed.

While the details will be described later, in the present embodiment,the selection of the display mode by the CPU 30 is performed based on anoperation input on the input unit 40 (mode selection unit), for example.When the first display mode is selected by the mode selection process,the CPU 30 displays the wearing simulation image (corrected simulationimage) on the monitor 50 by the process of S4. When the second displaymode is selected by the mode selection process, the CPU 30 displays thenon-wearing simulation in age (non-corrected simulation image) on themonitor 50 by the process of S4. The mode of display of the wearingsimulation image and the non-wearing simulation image is not limited tosuch that one image is selectively displayed. For example, the two typesof simulation images may be displayed on the same screen simultaneously.

In the process of S4, display control for modifying the distance fromthe eyeball model image 101 to the first simulation image 105 may beperformed. For example, the CPU 30 may perform a process of moving thefirst simulation image 105 to a position on the monitor 50 designated bya pointing device and the like. Further, the CPU 30 may also perform aprocess (such as the process of S3) of generating a simulation imagewhile the distance between the examinee's eye and the target duringsimulation is modified in conjunction with the distance between theeyeball model image 101 and the first simulation image 105, and thedisplay control process (S4) for updating the simulation image on themonitor 50 to an image generated by the simulation after modification ofthe distance between the examinee's eye and the target. In this way, theexaminer can intuitively modify the distance between the examinee's eyeand the target during simulation.

In the present embodiment, the characteristics information imagesindicating the information about the eye optical system characteristicsof the examinee's eye are displayed in association with the locations onthe eyeball model image 101. In a specific example, in FIG. 3, thecorneal information image 102 and the intraocular information image 103are displayed in association with the cornea and the inside of theeyeball, respectively, of the eyeball model image 101. Further, in thepresent embodiment, refractivity information images 109 a and 109 b andan anterior segment image 111 in photopic vision or twilight vision aredisplayed in association with the anterior segment of the eyeball modelimage 101. In the processing device 1 according to the presentembodiment, the respective characteristics information images aredisplayed in association with the locations on the eyeball model image101. Thus, even a person not familiar with ophthalmologic imagery caneasily figure out the information of which location of the examinee'seye is being indicated by each characteristics information image.

A corneal information image 107 two-dimensionally shows characteristicsconcerning the corneal anterior surface shape of the examinee's eye. Thecorneal information image 107 is generated based on the cornealinformation acquired by the process of S1 (such as the three-dimensionalshape data, curvature data, refraction data, and aberration data of thecorneal anterior surface). As the corneal information image 107, inaddition to the curvature map of the corneal anterior surface shown inFIG. 3, a corneal anterior surface shape map, a refraction map (i.e., acorneal refraction map), or an aberration analysis map may be used. Therefraction map shows a refractive distribution of the examinee's eye inthe examination range. Particularly, the corneal refraction map shows arefractive distribution on the corneal anterior surface.

An anterior segment reflected image of a corneal shape measurementtarget may be used as the corneal information image 107. An example ofthe conical shape measurement target is a ring pattern age, such as aplacido ring, projected on the examinee's eye by the anterior segmentmeasuring apparatus 10. Further, a corneal cross-sectional image, animage showing an analysis result with respect to the cornealcross-sectional image, and the like may be used as the cornealinformation image 107. The corneal cross-sectional image may be an imagecaptured by anterior segment OCT, a Scheimpflug camera, and the like,for example.

The corneal information age 107 is displayed in association with thecornea in the eyeball model image 101. Thus, even a person not familiarwith ophthalmologic imagery can easily figure out that the cornealinformation image 107 shows the state of the cornea. For example, if amap displayed as the corneal information image 107 is disturbed, it canbe inferred that there might be corneal abnormality.

An intraocular information image (crystalline lens information) 108mainly shows characteristics concerning at least one of opacity andrefraction in the examinee's eye two-dimensionally. The intraocularinformation image 108 is generated based on the intraocular informationacquired by the process of S1. Examples of the intraocular informationimage 108 concerning opacity in the examinee's eye include aretro-illumination image generated based on the image data of aretro-illumination image, and an image showing an analysis result of theretro-illumination image. In the retro-illumination image, the shape ofopacity in the pupil is shown. Thus, the retro-illumination image andthe like can be used to confirm the presence or absence of opacity andits degree in the optic media of the examinee's eye.

The intraocular information image 108 may be a map image (such as arefraction map (i.e., an intraocular refraction map), an aberration map(i.e., an intraocular aberration map), or a high-order aberration map(i.e., an intraocular high-order aberration map)) generated based onrefractivity information such as refraction data and aberration data)about the inside of the examinee's eye except for the corneal anteriorsurface. The intraocular refraction map shows a refractive distributionin the examinee's eye except for the corneal anterior surface. Theaberration map shows a distribution of aberration caused in anexaminee's eye examination range. Particularly, the intraocularaberration map shows a distribution of aberration caused in theexaminee's eye except for the corneal anterior surface. The high-orderaberration map is a two-dimensional map concerning a third or higherorder of aberration caused in the examinee's eye examination range.Particularly, the intraocular high-order aberration map is a mapconcerning a third or higher order of aberration caused in theexaminee's eye except for the corneal anterior surface.

The intraocular refraction map (which is an example of the intraocularrefractivity information image) may be obtained by using, for example, adifferential between the refractive distribution in the examinee's eyeas a whole and the refractive distribution in the corneal anteriorsurface (see JP-A-2006-26242 for more detail). The intraocularrefractivity information image is an image concerning the refractivedistribution corresponding to refraction in the examinee's eye exceptfor the corneal anterior surface, and is an example of the intraocularinformation image 108.

The intraocular information image 108 is displayed in association withthe inside of the eyeball in the eyeball model image 101. Thus, even aperson not familiar with ophthalmologic imagery can easily figure outthat the intraocular information image 108 shows the state inside theeyeball. Particularly, in the present embodiment, as shown in FIG. 3,the intraocular information image 108 is displayed in association withthe crystalline lens in the eyeball model image 101. The crystallinelens is a typical location where opacity or refractive error may becaused in the eye. Accordingly, even a person not familiar withophthalmologic imagery can easily figure out that the intraocularinformation image 108 has a strong relationship with the state of thecrystalline lens in particular.

When an unclear target image is formed in the simulation images 105 and106, it may be difficult to identify the cause of the unclear targetimage from the content of the corneal information image 107. In thiscase, the cause of the unclear target image may be shown in the contentof the intraocular information image 108. For example, if theintraocular information image 108 shows that there is opacity in theexaminee's eye, it may be inferred that unclarity may remain in thetarget image even if the refractive error of the examinee's eye iscorrected. Also, if the intraocular information image 108 shows adisturbed refractive distribution, for example, it can be inferred thatirregular astigmatism and the like due to refractive error in theexaminee's eye may be the cause of the unclear target image.

The refractivity information image 109 also two-dimensionally showscharacteristics concerning refraction of the examinee's eye as a wholein the examination range. The refractivity information image 109 isgenerated based on the refractivity information of the examinee's eye asa whole (such as refraction data and aberration data) acquired by of theprocess of S1. The mode of the refractivity information image 109includes, for example, a total eye refraction map, a wavefront map, aneyeglass-uncorrectable component map, and a Shack-Hartmann image. Therefractivity information image 109 shows the state of refraction of theexaminee's eye as a whole (entire examinee's eye). The total eyerefraction map shows a refractive distribution of the examinee's eye asa whole in the examination range.

A total eye refraction map 109 a, which is a mode of the refractivityinformation image 109, shows the distribution of refraction of theexaminee's eye as a whole. An eyeglass-uncorrectable component map 109b, which is another mode of the refractivity information image 109,shows a distribution of a high-order (third order or higher) aberrationin the examination range. As shown in FIG. 3, the refractivityinformation image 109 may have various values attached concerning therefractive power of the examinee's eye. For example, a value indicatingthe refractive power of the examinee's eye may be attached to therefractivity information image 109 (see the map 109 a). For example,values of S, C, and A may be displayed. The pupil diameter may also bedisplayed in the refractivity information image 109. The valueindicating refraction and the pupil diameter may be displayed for eachof the case of photopic vision and the case of twilight vision. Theremay also be attached information of values indicating the magnitude ofthe uncorrectable component (such as the amount of high-order aberrationand an RMS (the root-mean-sum of a measurement value error with respectto an approximation curve of dioptre in the circumference direction)(see the map 109 b).

In FIG. 3, the total eye refraction map 109 a and theeyeglass-uncorrectable component map 109 b are simultaneously displayed.However, the process of S4 may be such that only one of the images isdisplayed.

The anterior segment image 111 shows at least the size of the pupil inthe simulation environment. In the present embodiment, when a simulationimage in photopic vision is displayed, the anterior segment image 111 inphotopic vision is displayed. When a simulation image in twilight visionis displayed, the anterior segment image 111 in twilight vision isdisplayed. In the anterior segment image 111, a measurement value of thepupil diameter may be additionally displayed.

The processing device 1 may be configured to switch the simulation imageand the anterior segment image 111 displayed on the monitor betweenthose concerning photopic vision and those concerning twilight vision.More specifically, the processing device 1 may be configured such that,when an image in one of the environments of photopic vision and twilightvision is being displayed, the displayed image is switched to the imagein the other environment on the basis of the input of a display switchsignal to the processing device 1. The display switch signal may beoutput through a predetermined operation with respect to the input unit40, such as selecting the simulation image or the anterior segment image111 on the screen using a pointing device and the like.

In order to express the correspondence between the location of theeyeball model image 101 and the characteristics information image,various display techniques may be used. For example, the correspondencemay be expressed by placing the characteristics information image inproximity to a corresponding location of the eyeball model image 101.Alternatively, the correspondence may be expressed by superposing thecharacteristics information image over a corresponding location of theeyeball model image 101. It is also possible to use a symbol (i.e., acorresponding graphic, such as a line, an arrow, or a balloon)indicating the correspondence between the characteristics informationimage and the eyeball model image 101.

For example, a plurality of characteristics information imagesassociated with various locations on the eyeball model image may bedisplayed in an arrangement corresponding to the arrangement of thevarious locations of the examinee's eye in the eyeball model image. Whena graphic (such as the graphics 102 to 104) is selected by the operationof the pointing device and the like, the mode of display of thecharacteristics information image corresponding to the selected locationon the eyeball model image 101 may be modified to denote theircorrespondence. For example, when a graphic on the eyeball model isselected, the characteristics information image corresponding to theselected location is emphasized by an increase in size or blinking, or acharacteristics information image that has been set for non-display inadvance may be pop-up displayed.

The display control process (S4) according to the present embodiment mayinclude a process of switching the mode of at least one image among thecharacteristics information images being displayed on the screen of themonitor 50. For example, as the intraocular information image 108, animage showing the opacity distribution of the crystalline lens (such asa retro-illumination image) is displayed. In this case, the intraocularinformation image 108 may be snitched to another mode of display, suchas a crystalline lens refraction map. The selection of the image ofwhich the display mode is switched may be performed by the CPU 30 on thebasis of an operation input to the input unit 40. A specific example ofthe operation input is placing the cursor of a pointing device over thecharacteristics information image. When the characteristics informationimage of which the display mode is to be switched is designated, thedisplay control process (S4) may cause the display of a list of indexinformation (such as image names and thumbnail images) of candidates ofdisplay modes after the switching. In this case, the CPU 30 causes thecharacteristics information image selected by the examiner from amongthe candidates to be newly displayed. The examiner may make a selectinginput via the input unit 40.

Further, as shown in FIG. 3, in the display control process (S4)according to the present embodiment, the CPU 30 causes a lens graphic110 representing a corrective lens (in FIG. 3, an eyeglass lens) to bedisplayed forwardly of the examinee's eye.

In the present embodiment, the display control process (S4) includes aprocess of controlling the display mode of the lens graphic 110 on themonitor 50 to one of a mode denoting the wearing of the eyeglass lenswith respect to the eyeball of the eyeball model image 101, and a modedenoting the non-wearing of the eyeglass lens with respect to theeyeball of the eyeball model image 101. For example, the location of thelens graphic 110 may be varied between the mode denoting the wearing ofthe eyeglass lens and the mode denoting the non-wearing of the eyeglasslens. More specifically, as shown in FIG. 3, the wearing of the eyeglasslens may be denoted by locating the lens graphic 110 at a forwardposition (such as the lens fit position) in the direction of the visualline of the eyeball of the eyeball model image 101. On the other hand,the non-wearing of the eyeglass lens may be denoted by locating the lensgraphic 110 at a position spaced apart from the visual line of theeyeball of the eyeball model image 101, or by not displaying the lensgraphic 110. Further, the degree of emphasis of the lens graphic 110 maybe varied between the mode denoting the wearing of the eyeglass lens andthe mode denoting the non-wearing of the eyeglass lens. For example,when denoting the wearing of the eyeglass lens, the lens graphic 110 maybe emphasized more than when denoting the non-wearing of the eyeglasslens. The emphasized display includes, for example, increasing thecontrast of the lens graphic 110, and increasing the thickness of theedge line of the lens graphic 110.

In the present embodiment, the CPU so selects the display mode of thelens graphic 110 on the basis of the common operation input to theoperation for selecting the above-described simulation image displaymode. Thus, when the wearing simulation image is displayed in the firstdisplay mode, the lens graphic 110 denoting the wearing of the eyeglasslens is simultaneously displayed on the monitor 50. On the other hand,when the non-wearing simulation image is displayed in the second displaymode, the display mode of the lens graphic 110 on the monitor 50 becomesthe non-wearing denoting mode. In this way, according to the presentembodiment, the lens graphic 110 display mode and the simulation imagedisplay mode are switched in conjunction with each other. Accordingly,the processing device 1 allows the examiner to readily figure out, basedon the lens graphic 110 display mode, whether the wearing simulationimage or the non-wearing simulation image is being displayed on themonitor 50.

Further, in the present embodiment, when the correction data used forsimulation is not acquired in the process of S2, the lens graphic 110may not be displayed. Obviously, the lens graphic 110 may be displayedregardless of whether the correction data is acquired. As shown in FIG.3, the correction data, such as prescription values, may be displayedtogether with the lens graphic 110.

The display control process (S4) may also include a process of rotatinga graphic related to the cylindrical axis of the lens (such as a lensgraphic per se, or the cylindrical axis on the lens graphic) in the lensgraphic 110. For example, when the examiner designates the orientationof the cylindrical axis (cylindrical axis angle) after movement using apointing device, the graphic related to the cylindrical axis may bemoved. The processing device 1 may also be configured to modify, duringsimulation, the correction data concerning the cylindrical axis inconjunction with the rotation of the graphic related to the cylindricalaxis. Thus, the CPU 30 may perform, for example, a process of newlygenerating the simulation images 105 and 106 on the basis of thecorrection data of the designated cylindrical axis angle, and a processof updating the simulation image on the monitor to the newly generatedimages while rotating the graphic related to the cylindrical axis. Theexaminer, for example, can confirm the simulation images 105 and 106with the modified lens cylindrical axis through the operation ofrotating the graphic related to the cylindrical axis. This function isparticularly useful when, for example, examining correction data havinga proper cylindrical axis by simulation with regard to the examinee'seye of which the astigmatic axial angle is varied between photopicvision and twilight vision.

The process of S4 may include display control for modifying the distancefrom the eyeball model image 101 to the lens graphic 110 in the displaymode denoting the wearing of the eyeglass lens. Further, the CPU 30 mayperform a process of generating the simulation image while modifying theinterval of the examinee's eye and the location of the corrective lensduring simulation in conjunction with the distance between the eyeballmodel image 101 and the lens graphic 110 (such as the process of S3),and the display control process (S4) of updating the simulation image onthe monitor 50 to the simulation image generated using the modifieddistance between the examinee's eye and the corrective lens. The monitor50 may also display information (such as numerical values) indicatingthe interval of the examinee's eye and the location of the correctivelens during simulation.

It may be difficult to know whether a state of a proper lens beingprescribed is being simulated just by looking at the simulation image.One reason is that, when the examinee's eye has irregular astigmatism,the image may be blurred even if refraction of the examinee's eye isproperly corrected. In this regard, the CPU 30 of the processing device1 according to the present embodiment causes the characteristicsinformation images concerning the characteristics of various locationsof the examinee's eye to be displayed in association with the locationson the eyeball model image 101. Thus, even a person not familiar withophthalmologic imagery can readily know the information about whichlocation of the examinee's eye is being shown by each characteristicsinformation image. Further, the characteristics information image andthe eyeball model image 101 are displayed together with the simulationimages 105 and 106. Thus, when the simulation image is unclear, forexample, the examiner can readily intuitively know the reason from thecharacteristics information image.

The technology according to the present disclosure has been describedwith reference to embodiments. The technology of the present disclosureis not limited to the embodiments and may be variously modified. Forexample, in the embodiments, the first simulation image 105 and thesecond simulation image 106 are simultaneously displayed on the samescreen. Alternatively, the processing device 1 may be configured todisplay only one of the two types of simulation images.

The embodiments of the present disclosure may include a first to asixteenth ophthalmic image processing methods and a first storage mediumas follows.

The first ophthalmic image processing method is an ophthalmic imageprocessing method for displaying examinee's eye characteristics obtainedby an optometry apparatus, the method including performing, in anophthalmic information processing device, an acquisition step ofacquiring information about the characteristics of the examinee's eyeincluding at least corneal information about the anterior surface shapeof the cornea of the examinee's eye, and refractivity information aboutrefraction of the examinee's eye as a whole; a generating step ofgenerating a simulation image of a target image that is formed at thefundus of the examinee's eye, using at least the refractivityinformation obtained in the acquisition step; and a display control stepof causing an eyeball model image showing an eyeball structure and thesimulation image obtained in the generating step to be simultaneouslydisplayed on a display device, and further causing a corneal informationimage based on the corneal information obtained in the acquisition stepto be simultaneously displayed on the display device in association withthe cornea on the eyeball model image.

The second ophthalmic image processing method is the first ophthalmicimage processing method wherein the acquisition step further includesacquiring intraocular information about at least one of opacity in theexaminee's eye and refraction in the examinee's eye except for thecorneal anterior surface, and wherein the display control step furtherincludes causing an intraocular information image based on theintraocular information obtained in the acquisition step to be displayedon the display device in association with the inside of the eyeball onthe eyeball model image and simultaneously with the eyeball model image,the simulation image, and the corneal information image.

The third ophthalmic image processing method is the second ophthalmicimage processing method wherein the acquisition step includes acquiring,as the intraocular information about the opacity in the examinees eye,at least a retro-illumination image of the examinee's eye, and thedisplay control step includes causing the retro-illumination imageobtained in the acquisition step to be displayed as the intraocularinformation image.

The fourth ophthalmic image processing method is the second ophthalmicimage processing method wherein the acquisition step includes acquiring,as the intraocular information, at least the intraocular informationabout refraction in the examinee's eye except for the corneal anteriorsurface, and the display control step includes causing an intraocularrefractivity information image concerning a refractive distributionbased on the intraocular information to be displayed as the intraocularinformation image.

The fifth ophthalmic image processing method is the fourth ophthalmicimage processing method wherein the display control step includescausing a corneal refraction map showing the refractive distribution onthe corneal anterior surface to be displayed as the corneal informationimage based on the corneal information, and further causing anintraocular refraction map which is a refraction map of the inside ofthe examinee's eye except for the cornea to be displayed as theintraocular refractivity information image.

The sixth ophthalmic image processing method is the first ophthalmicimage processing method further including performing a correction dataacquisition step of acquiring correction data of a corrective lens forcorrecting the refractive error of the examinee's eye, wherein thegenerating step includes generating a wearing simulation image which isthe simulation image of the target image formed at the fundus of theexaminee's eye in a corrective lens wearing state, using at least therefractivity information and the correction data.

The seventh ophthalmic image processing method is the sixth ophthalmicimage processing method including a mode selecting step of selecting onedisplay mode from a plurality of display modes including a first displaymode for displaying the simulation image with respect to the examinee'seye wearing a corrective lens and a second display mode for displayingthe simulation image with respect to the examinee's eye not wearing acorrective lens, wherein the generating step includes generating thecorrected simulation image and a non-wearing simulation image which is asimulation image with respect to the examinee's eye not wearing acorrective lens, wherein the display control step includes causing, whenthe first display mode is selected in the mode selecting step, thecorrected simulation image to be displayed on the display devicesimultaneously with the eyeball model image, the simulation image, andthe corneal information image, or, when the second display mode isselected in the mode selecting step, causing the non-correctedsimulation image to be displayed on the display device simultaneouslywith the eyeball model image, the simulation image, and the cornealinformation image.

The eighth ophthalmic image processing method is the seventh ophthalmicimage processing method wherein the display control step includescausing a lens graphic representing the corrective lens to be displayedat a lens fit position in the eyeball model image simultaneously withthe wearing simulation image.

The ninth ophthalmic image processing method is the first ophthalmicimage processing method wherein the display control step includescausing a refractivity information image which is a refractivityinformation image based on the refractivity information and whichconcerns a refractive distribution of the examinee's eye as a whole inthe examination range to be displayed on the display devicesimultaneously with the eyeball model image, the simulation image, andthe corneal information image.

The tenth ophthalmic image processing method is the ninth ophthalmicimage processing method wherein the display control step includescausing an aberration map showing a distribution of aberration caused inthe examination range of the examinee's eye to be displayed on thedisplay device as the refractivity information image.

The eleventh ophthalmic image processing method is the tenth ophthalmicimage processing method wherein the display control step includescausing a high-order aberration map which is a two-dimensional mapconcerning a third or higher order of aberration caused in theexamination range of the examinee's eye to be displayed on the displaydevice.

The twelfth ophthalmic image processing method is the ninth ophthalmicimage processing method wherein the display control step includescausing a total eye refraction map showing a distribution of refractionof the examinee's eye as a whole in the examination range to bedisplayed on the display device as the refractivity information image.

The thirteenth ophthalmic image processing method is the firstophthalmic image processing method wherein the generating step includesgenerating, as the simulation image, a first simulation image simulatedwith regard to a first target which is a subjective examination target,and a second simulation image simulated with regard to a second targetwhich is a point image, and wherein the display control step includescausing the first simulation image and the second simulation image to bedisplayed on the display device simultaneously with the eyeball modelimage, the simulation image, and the corneal information image.

The fourteenth ophthalmic image processing method is the firstophthalmic image processing method wherein the generating step includesgenerating a simulation image in photopic vision based on data of apupil diameter of the examinee's eye in photopic vision, and asimulation image in twilight vision based on data of the pupil diameterof the examinee's eye in twilight vision, and wherein the displaycontrol step includes causing the anterior segment image of theexaminee's eye in photopic vision to be displayed simultaneously withthe simulation image in photopic vision in association with the anteriorsegment of the eyeball model image, and causing the anterior segmentimage of the examinee's eye in twilight vision to be displayedsimultaneously with the simulation image in twilight vision inassociation with the anterior segment of the eyeball model image.

The fifteenth ophthalmic image processing method is the first ophthalmicimage processing method wherein the display control step includescausing a corresponding graphic for indicating a correspondencerelationship between various locations of the eyeball model image andimages associated with the various locations on the eyeball model imageto be displayed on the display device simultaneously with the eyeballmodel image, the simulation image, and the corneal information image.

The sixteenth ophthalmic image processing method is the first ophthalmicimage processing method wherein the display control step includescausing images associated with various locations on the eyeball modelimage to be displayed on the display device in an arrangementcorresponding to an arrangement of various locations of the examinee'seye in the eyeball model image.

The first storage medium is a storage medium having an ophthalmicinformation processing program for displaying examinee's eyecharacteristics obtained by an optometry apparatus stored therein, theophthalmic information processing program, when executed by a processorof the ophthalmic information processing device, causing the ophthalmicinformation processing device to perform an acquisition step ofacquiring information about the characteristics of the examinee's eyeincluding at least corneal information about an anterior surface shapeof the cornea of the examinee's eye, and refractivity information aboutrefraction of the examinee's eye as a whole; a generating step ofgenerating a simulation image of a target image that is formed at thefundus of the examinee's eye, using at least the refractivityinformation obtained in the acquisition step; and a display control stepof causing an eyeball model image showing an eyeball structure and thesimulation image obtained in the generating step to be simultaneouslydisplayed on a display device, and further causing a corneal informationimage based on the corneal information obtained in the acquisition stepto be simultaneously displayed on the display device in association withthe cornea on the eyeball model image.

The foregoing detailed description has been presented for the purposesof illustration and description. Many modifications and variations arepossible in light of the above teaching. It is not intended to beexhaustive or to limit the subject matter described herein to theprecise form disclosed. Although the subject matter has been describedin language specific to structural features and/or methodological acts,it is to be understood that the subject matter defined in the appendedclaims is not necessarily limited to the specific features or actsdescribed above. Rather, the specific features and acts described aboveare disclosed as example forms of implementing the claims appendedhereto.

What is claimed is:
 1. An ophthalmic image processing method comprising:acquiring information about characteristics of an examinee's eyeincluding corneal information about the corneal anterior surface shapeof the examinee's eye, and refractivity information about refraction ofthe examinee's eye as a whole; generating a simulation image of a targetimage formed at fundus of the examinee's eye using the refractivityinformation; and simultaneously displaying an eyeball model imageshowing an eyeball structure, the simulation image, and a cornealinformation image associated with the cornea on the eyeball model imageand corresponding to the corneal information.
 2. The ophthalmic imageprocessing method according to claim 1, comprising: acquiringintraocular information about at least one of opacity in the examinee'seye and refraction in the examinee's eye except for the corneal anteriorsurface; and displaying an intraocular information image correspondingto the intraocular information in association with the inside of theeyeball of the eyeball model image simultaneously with the eyeball modelimage, the simulation image, and the corneal information image.
 3. Theeye ophthalmic image processing method according to claim 2, comprising:acquiring a retro-illumination image of the examinee's eye as theintraocular information about the opacity in the examinee's eye; anddisplaying the retro-illumination image as the intraocular informationimage.
 4. The ophthalmic image processing method according to claim 2,comprising: acquiring at least intraocular information about refractionin the examinee's eye except for the corneal anterior surface as theintraocular information; and displaying an intraocular refractivityinformation image concerning a refractive distribution corresponding tothe intraocular information as the intraocular information image.
 5. Theophthalmic image processing method according to claim 4, comprising:displaying a corneal refraction map indicating a refractive distributionon the corneal anterior surface as the corneal information imagecorresponding to the corneal information; and displaying an intraocularrefraction map that is a refraction map of the inside of the examinee'seye except for the co ea as the intraocular refractivity informationimage.
 6. The ophthalmic image processing method according to claim 1,further comprising: acquiring correction data for a corrective lens forcorrecting a refractive error of the examinee's eye; and generating awearing simulation image that is a simulation image of the target imageformed at the fundus of the examinee's eye wearing the corrective lens,using the refractivity information and the correction data.
 7. Theophthalmic image processing method according to claim 6, furthercomprising: selecting one display mode from a plurality of display modesincluding a first display mode for displaying the wearing simulationimage, and a second display mode for displaying a non-wearing simulationimage that is a simulation image with respect to the examinee's eye notwearing the corrective lens; generating the wearing simulation image andthe non-wearing simulation image; and displaying the wearing simulationimage simultaneously with the eyeball model image, the simulation image,and the corneal information image when the first display mode isselected, or displaying the non-wearing simulation image simultaneouslywith the eyeball model image, the simulation image, and the cornealinformation image when the second display mode is selected.
 8. Theophthalmic image processing method according to claim 7, comprisingdisplaying a lens graphic representing the corrective lens at a lens fitposition in the eyeball model image simultaneously with the wearingsimulation image.
 9. The ophthalmic image processing method according toclaim 1, comprising displaying a refractivity information imageconcerning a distribution of refraction of the examinee's eye as a wholein the examination range and based on the refractivity information,simultaneously with the eyeball model image, the simulation image, andthe corneal information image.
 10. The ophthalmic image processingmethod according to claim 9, comprising displaying an aberration mapshowing a distribution of aberration caused in the examination range ofthe examinee's eye as the refractivity information image.
 11. Theophthalmic image processing method according to claim 10, comprisingdisplaying a high-order aberration map that is a two-dimensional mapconcerning a third or higher order of aberration caused in theexamination range of the examinee's eye.
 12. The ophthalmic imageprocessing method according to claim 9, comprising displaying a totaleye refraction map indicating a distribution of refraction of theexaminee's eye as a whole in the examination range as the refractivityinformation image.
 13. The ophthalmic image processing method accordingto claim 1, comprising: generating, as the simulation image, a firstsimulation image obtained by simulation using a first target that is asubjective examination target and a second simulation image obtained bysimulation using a second target that is a point image; and displayingthe first simulation image and the second simulation imagesimultaneously with the eyeball model image, the simulation image, andthe corneal information image.
 14. The ophthalmic image processingmethod according to claim 1, comprising: generating the simulation imagein photopic vision based on data of a pupil diameter of the examinee'seye in photopic vision, and a simulation image in twilight vision basedon the data of the pupil diameter of the examinee's eye in twilightvision; and displaying the simulation image in photopic vision and theanterior segment image of the examinee's eye in photopic vision inassociation with the anterior segment of the eyeball model image, anddisplaying the simulation image in twilight vision and the anteriorsegment image of the examinee's eye in twilight vision in associationwith the anterior segment of the eyeball model image.
 15. The ophthalmicimage processing method according to claim 1, comprising displaying acorresponding graphic for indicating a correspondence relationshipbetween various locations of the eyeball model image and imagesassociated with the various locations of the eyeball model imagesimultaneously with the eyeball model image, the simulation image, andthe corneal information image.
 16. The ophthalmic image processingmethod according to claim 1, comprising displaying images associatedwith various locations of the eyeball model image in an arrangementcorresponding to an arrangement of various locations of the examinee'seye in the eyeball model image.
 17. A non-transitory storage mediumhaving a computer program for causing a computer to function as anophthalmic information processing device stored therein, the ophthalmicinformation processing device performing: acquiring information aboutthe characteristics of an examinee's eye including corneal informationabout a corneal anterior surface shape of the examinee's eye andrefractivity information about refraction of the examinee's eye as awhole; generating a simulation image of a target image formed at thefundus of the examinee's eye using the refractivity information; andsimultaneously displaying an eyeball model image showing an eyeballstructure, the simulation image, and a corneal information imageassociated with the cornea on the eyeball model image and correspondingto the conical information.